System and method for droplet formation and manipulation using ferrofluids

ABSTRACT

A microfluidic device for forming droplets includes at least one ferrofluid reservoir disposed in the microfluidic device and containing a ferrofluid therein. The microfluidic device includes a continuous-phase reservoir disposed in the microfluidic device and containing an oil phase therein and one or more microfluidic channels connecting between the at least one ferrofluid reservoir and the continuous-phase reservoir, the continuous-phase reservoir comprising a step region having an increased height as compared to a height of the one or more microfluidic channels. To form droplets an externally applied magnetic field is applied to the device to pull the ferrofluid into the continuous-phase reservoir, whereby droplets are formed at step region.

RELATED APPLICATION

This Application is a continuation of U.S. application Ser. No.15/767,979 filed on Apr. 12, 2018, issued as U.S. Pat. No. 10,688,453,which is a U.S. National Stage filing under 35 U.S.C. § 371 ofInternational Application No. PCT/US2016/056148, filed Oct. 7, 2016,which claims priority to U.S. Provisional Patent Application No.62/241,917 filed on Oct. 15, 2015, which are hereby incorporated byreference. Priority is claimed pursuant to 35 U.S.C. §§ 119, 371 and anyother applicable statute.

STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH AND DEVELOPMENT

This invention was made with Government support under Grant Number1332275, awarded by the National Science Foundation. The Government hascertain rights in the invention.

FIELD OF THE INVENTION

The technical field generally relates to methods and devices thatutilize magnetic forces to generate droplets from reagents mixed with aferrofluid. Reagents may include chemical species, nucleic acid (e.g.,DNA), cells, drugs, and the like.

BACKGROUND

Lab-on-chip devices are becoming increasing explored and used incommercial applications. Typically, these devices are integrated into amicrofluidic platform that utilize small volumes of reagents totransport, mix, and perform reactions that used to be performed inlarger, bench-top settings. Lab-on-chip devices are known that usedroplets as small reaction vessels that contain reagents and/or cells.In typical droplet-based devices, the droplets are formed by a pinchingflow of oil around an aqueous phase to generate aqueous droplets oremulsions carried in an oil-based medium. In current droplet-baseddevices, various pumping devices (e.g., syringe pumps) are also requiredto pump the aqueous and oil phase components through the device togenerate the emulsions. These pumps often require tuning of the flowrates to ensure that droplets of a particular size and composition areformed. Also, the bulky nature of pressure pumps or syringe pumps leadsto more complex and larger devices which are less suitable forpoint-of-care assays as well as difficulty to simply load samples andreagents and mix them in a complete system.

More recently, ferrofluids, or fluids that contain suspended magneticnanoparticles, have been used in many biomedical applications includingvarious pumping and valving applications. See, Pamme, Magnetism andmicrofluidics, Lab Chip, 6, 24-38 (2006). For example, ferrofluids havebeen used as a tool for adjusting the size of droplets when magneticfluids are applied in a T-junction and flow focusing droplet generators.See, Liu et al., Numerical and experimental investigations of theformation process of ferrofluid droplets, Microfluid Nanofluid, 11,177-187 (2011). For example, Liu et al. have studied formation offerrofluid droplets, the velocity field and droplet size in a pressuredriven flow focusing device under influence of a uniform magnetic field.See Liu et al., Numerical study of the formation process of ferrofluiddroplets, Physics of Fluids, 23, 072008 (2011). Tan et al. have alsostudied the effect of an external magnet (and also magnetic flux densitygradient) and flow rates on droplet size in a pressure driven T-junctiondroplet generator. See Tan et al., Formation and manipulation offerrofluid droplets at a microfluidic T-junction, J. Micromech.Microeng. 20, 045004, (2010). However, a need for accurate pumps fordroplet generation in these pressure driven systems limits applyingthese droplet generators as portable devices for point-of-careapplications. There is a need for an alternative droplet generatingmodality that can be utilized to encapsulate reagents and otherconstituents (e.g., cells) within droplets without the need foraccompanying pumping and associated fluidic components associated withtraditional droplet-based devices.

SUMMARY

In one embodiment, an emulsification or droplet generation method isdisclosed that can be performed at the micro-scale using a microfluidicdevice and magnetic field induced movement of the fluid containing aferrofluid therein. Using either a permanent magnet or an electromagnet,the ferrofluid is pulled through the one or more microfluidic channelsthat are coupled to one or more ferrofluid reservoirs. The one or moremicrofluidic channels lead to a continuous-phase reservoir. A step isformed at the transition from the one or more microfluidic channels tothe continuous-phase reservoir and is the location where droplets areformed. The ferrofluid makes the solution susceptible to a magneticfield, creating a body force within the fluid. Therefore, by adjustingthe magnetic field strength (e.g., by locating a permanent magnet, orenergizing an electromagnet) one is able to draw fluid to the stepinterface, where surface tension leads to fluid breakup; generatingdroplets without using external pumps as is required for conventionalmethods.

In another embodiment, a method of forming droplets in a microfluidicdevice using a ferrofluid includes providing a microfluidic devicehaving one or more ferrofluid reservoirs containing a ferrofluid thereinand a continuous-phase reservoir containing an oil therein, wherein theone or more ferrofluid reservoirs are coupled to the continuous-phasereservoir via one or more microfluidic channels, the continuous-phasereservoir comprising a step region having an increased height ascompared to a height of the one or more microfluidic channels. Anexternal magnetic field is applied to the microfluidic device, whereinthe external magnetic field moves the ferrofluid solution along the oneor more microfluidic channels and generates droplets in thecontinuous-phase reservoir.

In another embodiment, a method of forming droplets in a microfluidicdevice using a ferrofluid includes providing a microfluidic devicehaving one or more ferrofluid reservoirs containing an organicferrofluid therein and a continuous-phase reservoir containing anaqueous solution therein, wherein the one or more ferrofluid reservoirsare coupled to the continuous-phase reservoir via one or moremicrofluidic channels, the continuous-phase reservoir comprising a stepregion having an increased height as compared to a height of the one ormore microfluidic channels. An external magnetic field is applied to themicrofluidic device, wherein the external magnetic field moves theorganic ferrofluid solution along the one or more microfluidic channelsand generates organic droplets in the continuous-phase reservoir.

In still another embodiment, a microfluidic device for forming dropletsincludes at least one ferrofluid reservoir disposed in the microfluidicdevice and containing a ferrofluid therein. The device includes acontinuous-phase reservoir disposed in the microfluidic device andcontaining an oil phase therein. One or more microfluidic channelsconnect between the at least one ferrofluid reservoir and thecontinuous-phase reservoir, the continuous-phase reservoir comprising astep region having an increased height as compared to a height of theone or more microfluidic channels. A moveable external magnet is locatedadjacent to the microfluidic device.

In still another embodiment, an implantable microfluidic device fordelivering a drug to a subject includes a ferrofluid reservoir disposedin the microfluidic device and containing a ferrofluid and drug therein.A continuous-phase reservoir is disposed in the microfluidic device andcontains an oil phase therein, the continuous-phase reservoir containinga permeable membrane therein through which the drug passes. One or moremicrofluidic channels connect between the ferrofluid reservoir and thecontinuous-phase reservoir, the continuous-phase reservoir comprising astep region having an increased height as compared to a height of theone or more microfluidic channels. A permanent magnet is disposedadjacent to the permeable membrane on a first side of the device. Anelectromagnet is disposed on a second (opposite) side of the device andis connected to driver circuitry configured to power the electromagnet.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A illustrates a side, schematic view of a microfluidic deviceaccording to one embodiment. FIG. 1A illustrates droplets being formedat a step in channel height due to the gradient of the magnetic field.

FIG. 1B illustrates a top view of the microfluidic device of FIG. 1A.

FIG. 1C illustrates a side view of a microfluidic device according toanother embodiment. In this embodiment, which employs a parallelconfiguration, there are multiple microfluidic channels that connect theferrofluid reservoir to the continuous-phase reservoir.

FIG. 1D illustrates a top view of another embodiment of a microfluidicdevice. In this embodiment, there are separate sample/reagent reservoirsthat connect to a common microfluidic channel that leads to thecontinuous-phase reservoir.

FIG. 1E illustrates a side view of a microfluidic device according toone embodiment.

FIG. 1F illustrates a three dimensional perspective view of a ferrofluidreservoir connected to a continuous phase reservoir via a singlemicrofluidic channel. A terraced transition region is also illustrated.

FIG. 2 illustrates a close-up side schematic view of the intersectionbetween a microfluidic channel and the stepped region of the continuousphase reservoir.

FIG. 3A illustrates an embodiment of a stage or track that is used tomove an external permanent magnet to various positions in the xdirection relative to the microfluidic device. The magnet may also bemoved in the z direction.

FIG. 3B illustrates an embodiment of a stage or track that is used tomove an external permanent magnet to various positions in the x and ydirection relative to the microfluidic device. The magnet may also bemoved in the z direction.

FIG. 3C illustrate an embodiment of a microfluidic device that is usedwith one or more electromagnets to apply an external magnetic field H tothe microfluidic device.

FIG. 4 illustrates an external permanent magnet being placed a distance(D) from the step of the continuous phase reservoir.

FIG. 5A illustrates a graph showing the droplet generation rate of themicrofluidic device as a function of magnet distance (D) for experimentsusing Pico-Surf™ as the continuous phase.

FIG. 5B illustrates a graph showing the droplet generation rate of themicrofluidic device as a function of magnet distance (D) for experimentsusing FC-40 as the continuous phase.

FIG. 5C illustrates a graph showing the droplet generation rate of themicrofluidic device as a function of magnetic flux density gradient fordiffering amounts of surfactant (2% Pico-Surf™, 5% Pico-Surf™, and 0%surfactant (Novec™ 7500)).

FIG. 6A schematically illustrates a side view of a microfluidic deviceaccording to another embodiment that includes a porous membrane.

FIG. 6B schematically illustrates a side view of a microfluidic deviceaccording to another embodiment that includes a porous membrane.

FIG. 6C illustrates one use of the microfluidic device being implantedinto the subject to deliver a drug or a medicament.

FIG. 6D illustrates another embodiment of an implantable microfluidicdevice that is used to deliver a drug or a medicament to a subject.

FIG. 6E illustrates a graph showing the volume of delivered drug atselected time intervals using an implantable microfluidic device of thetype illustrated in FIG. 6D. Also illustrated is a graph showing theON/OFF status of the electromagnet used to deliver a “low” dose of adrug or a “high” dose of a drug.

FIG. 7 illustrates a method of making a microfluidic device according toone embodiment.

FIG. 8A illustrates a graph illustrating the droplet generation rate asa function of volume fraction of magnetic nanoparticles. Alsoillustrated in the graph are photographs of the step region of themicrofluidic device showing nascent droplet generation. Below fractionsof around 0.005 once the droplet is formed, fluid starts refilling justbefore the step with the leading meniscus being located proximal to thestep around 60 μm. At fractions above 0.005 the ferrofluid startsrefilling right at the step.

FIG. 8B illustrates a graph illustrating the droplet generation rate asa function of magnetic flux density for different viscosities of thecontinuous phase (e.g., Novec™ 7500 and FC-40).

DETAILED DESCRIPTION OF THE ILLUSTRATED EMBODIMENTS

FIGS. 1A-1D schematically illustrate various embodiments of amicrofluidic device 10 for forming droplets 40. The microfluidic device10 includes at least one ferrofluid reservoir 12 that is disposed orformed in the microfluidic device 10. The at least one ferrofluidreservoir 12 contains a ferrofluid 15 or is configured to receive aferrofluid 15. As used herein, “ferrofluid” refers to a fluid thatcontains magnetic nanoparticles 17 suspended therein that confers thebulk fluid with magnetic properties. The size of the magneticnanoparticles 17 needs to be small enough such that the magneticnanoparticles 17 do not sediment out in response to gravity. Another wayof saying this is that the thermal energy is higher than thegravitational energy and magnetic energy due to an external magneticfield that would otherwise tend to cause sedimentation of the magneticnanoparticles 17, so they remain relatively evenly dispersed throughoutthe fluid. The magnetic nanoparticles 17 may vary in size but the sizesare generally within a few nm in diameter to around 100 nm in diameter.The size depends on the density of the fluid and the ironcontent/density of the magnetic nanoparticles 17. In some embodimentsdescribed herein, the ferrofluid 15 is aqueous-based. In otherembodiments, the ferrofluid is organic-based. This embodiment would beuseful for example to create magnetic droplets 40 that are polymerizedto form microparticles, when the pre-polymer requires an organic solventcontinuous phase. An example of an aqueous-based ferrofluid 15 includesEMG 408 available from Ferrotec, Co. which includes 10 nm magneticnanoparticles. Another example of an aqueous-based ferrofluid 15includes concentrated Feraheme (ferumoxytol available from amagpharmaceuticals) which includes 20 nm magnetic nanoparticles.Concentrated ferumoxytol is made by centrifuging about 1 ml offerumoxytol for 3 hours at 14,000 rpm and then the top 300 μl wasremoved to make the solution more susceptible to a magnetic field.Magnetic nanoparticles 17 in ferumoxytol are coated with polyglucosesorbitol carboxy-methyl ether which is a sugar and makes it a goodchoice for applications where direct contact of other materials withiron could cause problems.

In some embodiments there may be a single ferrofluid reservoir 12 suchas illustrated in FIG. 1A while in other embodiments there are multipleferrofluid reservoirs 12. FIG. 1A illustrates a mixture of theferrofluid 15 and a sample 2 being loaded into the ferrofluid reservoir12. The sample 2 may include a reagent, environmental sample, abiological fluid (e.g., bodily fluid), or even a cell-containing sample.The ferrofluid 15 and sample 2 may be pre-mixed or, as explained herein,the sample 2 and the ferrofluid 15 can be mixed prior to emulsifying ofthe sample 2 on the microfluidic device 10 by simply applying the sampleto the reservoir (e.g., by pipetting, capillary insertion, pouring)followed by mixing of the ferrofluid 15 and sample 2 by oscillating orlateral motions of an external magnet 30. FIG. 1D illustrates anembodiment where three ferrofluid reservoirs 12 a, 12 b, 12 c are used.One reservoir 12 a contains a ferrofluid mixed with a first reagent (orsample). A second reservoir 12 b contains a ferrofluid mixed with asecond reagent (or sample). A third reservoir 12 c contains a ferrofluidmixed with a third reagent (or sample).

The ferrofluid reservoir 12 may have a variety of different volumes. Forexample, the ferrofluid reservoir 12 may contain microliter or evenmilliliter sized volumes of ferrofluid 15. The ferrofluid reservoir 12may include an inlet 13 or opening that is used to fill (or re-fill) theferrofluid reservoir 12 as seen in FIG. 1E. In some instances the inlet13 can be open or exposed to the external environment so that it can bereadily filled. In other embodiments, the inlet 13 can be covered orsealed after being filled with ferrofluid 15. In yet anotheralternative, the inlet 13 can be fluidically coupled to a source offluid using tubing or the like.

Still referring to FIGS. 1A-1D, one or more microfluidic channels 14 arecoupled to the ferrofluid reservoir 12 and are used to transportferrofluid 15 to a droplet generation region as described herein. Theone or more microfluidic channels 14 may have varying lengths but theyare typically greater than 100 μm (e.g., 700 μm). In one embodiment, asingle microfluidic channel 14 can lead from a single ferrofluidreservoir 12 as seen in FIGS. 1A and 1B. Alternatively, multiplemicrofluidic channels 14 can lead from a single ferrofluid reservoir 12as is illustrated in FIG. 1C. This latter construction enables parallelprocessing so that large numbers of droplets 40 can be created andcollected. The cross-sectional shape of the microfluidic channels 14 aretypically rectangular or square and have widths and heights on the orderof tens of microns. For example, an exemplary width of the microfluidicchannel 14 may be on the order of around 65 μm with a height on theorder of around 30 μm, although other dimensions may be used.

The one or more microfluidic channels 14 carry the ferrofluid 15 fromthe ferrofluid reservoir 12 to a downstream continuous phase reservoir16. The continuous phase reservoir 16 contains the continuous phasefluid 19 in which the droplets are formed. In one embodiment, thecontinuous phase reservoir 16 is filled with an oil-based continuousphase fluid 19 while the ferrofluid 15 is aqueous-based. Alternatively,the continuous phase reservoir 16 may be filled with an aqueous-basedcontinuous phase fluid 19 while the ferrofluid 15 is organic oroil-based. The continuous phase reservoir 16 includes a step region 18wherein the height of the one or more microfluidic channels 14transitions to a larger height of the continuous phase reservoir 16. Asexplained herein, droplets 40 are formed at or adjacent to this stepregion 18. Referring to FIG. 2 , a step or wall 20 is formed thatextends generally transversely to the longitudinal axis of the one ormore microfluidic channels 14. The angle of the step or wall 20 may beformed with an angle θ that is equal to or less than 90°. The angle maybe less than 90° although at lower angles closer to 0° droplets will notreadily form. The continuous phase reservoir 16 has a height that ismuch larger than the height of the microfluidic channels 14 that leadthereto. For example, the height of the continuous phase reservoir 16may typically be within the range of 125-200 μm (e.g., 170 μm), althoughheights outside this range may also be used. Likewise, the width of thecontinuous phase reservoir 16 is much larger than the width of themicrofluidic channels 14 that lead thereto. The larger width and heightof the continuous phase reservoir 16 produces a chamber or region with alarge volume that can accommodate a large number of droplets oremulsions that are formed in the device as described herein. Thecontinuous phase reservoir 16 may include an outlet 22 (seen in FIG. 1E)that is used to extract the droplets or emulsions. The outlet 22 canalso be used to back-fill the device with the continuous phase (e.g.,oil). In some embodiments, the outlet 22 is open or exposed to theexternal environment. In other embodiments, the outlet 22 may be sealedsuch as with a layer of PDMS to seal the outlet 22.

With reference to FIGS. 1A-1F and FIG. 2 , in one preferred embodiment,the one or more microfluidic channels 14 lead first to a terraced ortransition region 24 prior to entering the continuous phase reservoir16. The terraced or transition region 24 has a height that is the sameas the microfluidic channel 14 that leads to the terraced or transitionregion 24 but a width that extends to the approximately same width asthe downstream continuous phase reservoir 16. The length of the terracedor transition region 24 is less than about 100 μm (e.g., 60 μm or 90 μmare exemplary lengths). The fluid that enters the terraced or transitionregion 24 is able to expand in the x-y direction. Once the fluid entersthe continuous phase reservoir 16 the fluid can expand in the zdirection to form the droplet or emulsion. It should be appreciated thatthe terraced or transition region 24 is optional and may be omittedentirely.

The microfluidic device 10 may be fabricated using conventionalprotocols for making polymer-based microfluidic devices such aspolydimethylsiloxane (PDMS)-based microfluidic devices. For example, theferrofluid reservoir(s) 12, the microfluidic channel(s) 14, and thecontinuous phase reservoir 16 may be formed in PDMS using softlithography methods (e.g., using photoresist and bonded class slides orcoverslips to form a mold) and the elastomeric portion 26 device may bebonded to a glass substrate 28 (e.g., glass slide or cover slip) usingoxygen plasma treatment or an optically cured adhesive (e.g., NOA 81;Norland Products, Inc., Cranbury, N.J.) as illustrated in FIG. 1E. Theinlet 13 and outlet 22 may also be formed by using a punch in theelastomeric PDMS layer 26. In some embodiments, the inlet 13 and theoutlet 22 may be open to the external environment. In other embodiments,the inlet 13 and/or the outlet 22 may be covered by another layer ofPDMS (not illustrated in FIG. 1E).

Referring to FIG. 1E, FIGS. 3A-3B, and FIG. 4 , the microfluidic device10 includes, as one embodiment, a moveable external magnet 30 that canbe positioned adjacent to the underside of the microfluidic device 10 todrive the ferrofluid 15 through the microfluidic device 10. The moveableexternal magnet 30 can be positioned at various locations as describedherein to achieve different droplet generation rates as well as startand stop droplet generation as desired. In one embodiment, a permanentmagnet can be used as the moveable external magnet 30 (e.g., D68 gradeN52 cylindrical magnet from K&J Magnetics, Inc.). The moveable externalmagnet 30 can be mounted on a moveable stage or track 32 that iscomputer-controlled and can move laterally adjacent to the microfluidicdevice 10. The moveable stage or track 32 moves the magnet 30 in the xdirection of FIG. 3A. In some embodiments, the moveable stage or track32 can move magnet in the y direction and the z direction. The moveableexternal magnet 30 is preferably located underneath the microfluidicdevice 10 and is located close enough to impart a magnetic field to theferrofluid 50 to effectuate movement of the same. In one aspect, themoveable external magnet 30 is immediately adjacent or in slight contactwith the substrate 28 of the microfluidic device 10. A small gap mayexist, however, between the magnet 30 and the substrate 28.

To fit in a handheld format, the microfluidic device 10 could sit on topof a track 32 that holds a moveable permanent magnet 30; whereby theposition of the magnet 30 can be electronically controlled, initiallylocated below the ferrofluid reservoir 12 and moving back and forth tomix the sample and ferrofluid 15, then the magnet 30 can beelectronically controlled to move down the track 32 pulling ferrofluid15 through the microfluidic channel 14 and into the step emulsificationregion 18 to generate droplets 40.

As an alternative to the track 32, the permanent magnet 30 may beaffixed to a stage or one or more actuators. A fast z-direction motionof the magnet 30 on the track 32, stage or actuator (or other movementdevice) away from the microfluidic device 10 can stop the motion ofdroplets 40 quickly. The magnet 30 could then be removed (or moved) fromthe region of the continuous phase reservoir 16 to allow imaging(fluorescence or spectrophotometric, or colorimetric) of a reactionoccurring in the droplets 40, the magnet 40 could also be moved moreslowly to pull droplets 40 following generation into an analysis regionlocated downstream of the continuous phase reservoir 16 for optical orelectronic analysis drop-by-drop. Alternatively, the imaging systemcould direct imaging illumination and collect light from a differentdirection as the magnet 30, and the magnet 30 could be held in place toensure minimal motion of droplets 40 during imaging.

In one embodiment, the microfluidic device 10 can be pre-loaded with oil(and optionally surfactant in certain embodiments) in the continuousphase reservoir 16 and ferrofluid 15 with reagent or sample in theferrofluid reservoir 12, such that only a single sample addition isrequired to perform an assay. In order to perform multistep assays orcombine reactive reagents in a timed manner another embodiment of theinvention includes a plurality of inlet reservoirs as seen in FIG. 1Deach with some amount of ferrofluid 15 to enable driving the motion ofthe flow, but with different reagent or sample components. Themicrofluidic channels 14 extending from different reservoirs 12 a, 12 b,12 c can then be merged immediately prior to the emulsification junctionor some distance upstream. The channels extending from the differentreservoirs could all merge at one point or sequentially merge if it isdesired to sequentially add reagent or sample in a desired order. In arelated embodiment, ferrofluid 15 from a plurality of reservoirs 12 aremerged into an intermediate reservoir following the motion of a magnet30, followed by mixing and/or an incubation step for a controlled timeperiod, and subsequently followed by droplet generation by a secondmotion of a magnet 30, 36 to draw ferrofluid 15 to a step region 18 asexplained herein.

The position of the moveable external magnet 30 as well as thedisplacement of the same may be adjusted or altered depending on theparticular application. Typically, the moveable external magnet 30 isheld stationary during at least part of the droplet formation process.By being held stationary, the magnetic field remains constant anddroplets 40 are generated at a substantially uniform rate. However, asexplained herein, the rate of droplet formation can be altered byadjusting the relative x position of the moveable external magnet 30.The formation of droplets 40 may also be stopped by moving the moveableexternal magnet 30 away from the microfluidic device 10 (e.g., in the zdirection) or by moving the external magnet 30 in the x directionsufficiently such that the ferrofluid 15 is not drawn toward the dropletgeneration. In addition, in some embodiments, the moveable externalmagnet 30 may be positioned beneath the ferrofluid reservoir 12 and ismoved back-and-forth under the ferrofluid reservoir 12. This process maybe used to mix the ferrofluid 15 and the sample.

In order to generate droplets 40, the moveable external magnet 30 ismoved beneath the continuous phase reservoir 16 and held stationary tobegin emulsifying the sample. In this embodiment, the moveable externalmagnet 30 is moved along a track in the x direction and is then heldstationary to enable the formation of droplets 40. The particulardistance at which the moveable external magnet 30 is held stationaryunder the continuous phase reservoir 16 may vary depending on thedesired droplet formation rate. The distance (D) of the external magnet30 is measured with respect to the step or wall 20 to the closest edgeor face of the external magnet 30 as seen in FIG. 4 . It has generallybeen found that higher droplet formation rates are achieved when thisseparation distance between the step or wall 20 and the external magnet30 is small. Larger separation distances produce lower dropletgeneration rates. The external magnet 30 is generally located a distance(D) that is less than about 0.5 cm from the step or wall 20 and morepreferably less than 0.25 cm from the step or wall 20.

FIGS. 5A and 5B illustrate the droplet generation rate that was obtainedat various magnet distances (D) using both Pico-Surf™ (FIG. 5A) andFC-40 (FIG. 5B) as the continuous phase. Increases in droplet generationrate are seen for magnet distances (D) that are less than 0.25 cm. Ofcourse, it should be understood that these distances were observed usingan external magnet 30 with a particular size and strength. Differentdistances can be expected based on external magnets 30 of differingmagnetic strengths.

After formation of the droplets 40, the stage or track device 32 maymove in the x, y, or z directions for post-formation manipulation. Forexample, movement in the z direction can be used to rapidly remove themagnetic field from affecting the droplets 40 or ferrofluid 15 in thedevice 10. For instance, droplet 40 movement may be stopped by movingthe moveable external magnet 30 away from the microfluidic device 10 inthe z direction. As an alternative to using a permanent magnet, anelectromagnet 34 (or multiple electromagnets) could be used as themoveable external magnet 30 as seen in FIG. 3C. For example, differentelectromagnets 34 or sections (EM1-EM11) could be activated (denoted by*) to provide for a moveable magnetic field H that can be used to drivethe ferrofluid 15 through the microfluidic device 10.

FIG. 6A illustrates another embodiment of the microfluidic device 10. Inthis embodiment, an elastomeric portion 26 (e.g., PDMS) is bonded to asubstrate 28 to define the ferrofluidic reservoir 12, the microfluidicchannel 14, and the continuous phase reservoir 16. Note that in thisembodiment, ferrofluidic reservoir 12 is completely contained in theelastomeric portion 26 and is pre-loaded with ferrofluid 15. Likewisethe continuous phase reservoir 16 is pre-loaded with the continuousphase fluid (e.g., aqueous-based fluid or oil-based fluid). In thisembodiment, a porous membrane 50 is defined in a region of thecontinuous phase reservoir 16. The porous membrane 50 contains porestherein that permit the selective passage of droplets 40 in response toa force that urges the droplets 40 through the porous membrane 50 to theopposing side. In the embodiment of FIG. 6A, the opposing side of theporous membrane 50 contains a second phase 52 which may be a solution orfluid into which the droplets 40 pass or merge into. In some instances,the second phase 52 may include a gas such as ambient air. For example,droplets 40 can still pass through the porous membrane 50 even without aliquid fluid located on the opposing side of the porous membrane 50.

The porous membrane 50 may be a PTFE or Nylon membrane havingmicrometer-sized pore sizes. An exemplary porous membrane 50 may includea Nylon membrane having 5 micron pore sizes available from BioDesign,Inc., Carmel, N.Y. The porous membrane 50 acts as a filter membrane thatis incorporated into the microfluidic device 10 and is in fluidcommunication with the continuous phase reservoir 16. Operation of thisembodiment of the microfluidic device 10 is similar to other embodimentswhere a moveable external magnet 30 is first placed adjacent to themicrofluidic device 10 to generate droplets 40. The generated droplets40, which have a known volume, can then be drawn out of the continuousphase reservoir 16 using a magnet 36. The magnet 36 may be the samemoveable external magnet 30 or a different magnet entirely. The magnet36 may be a permanent magnet or an electromagnet. The porous membrane 50acts as a passive valve that prevents the release of the droplets 40until a change in the magnetic field is induced in the system toovercome the interfacial energy increase that is needed to pull droplets40 through the porous membrane 50. The Nylon membrane 50 is hydrophilicallowing only ferumoxytol to pass through the membrane 50 and oil cannotpass. Other membranes 50 with different properties could also be used.

The embodiment of FIG. 6A could be used, for example, as a drug ormedicament delivery device 10 that selectively delivers medicine to asubject as illustrated in FIG. 6C (it should be understood that thedevice 10 may be located in other anatomical spaces). The microfluidicdevice 10 could be implanted within a patient (e.g., intramuscularly orsubcutaneously) and pre-loaded with the drug and ferrofluid 15. In someembodiments, the magnetic nanoparticles 17 that form the ferrofluid 15act as the drug and no separate drug is needed. An example of this isferumoxytol. In still other embodiments, a drug may be conjugated to themagnetic nanoparticle 17 (e.g., doxorubicin). In other embodiments, aseparate drug is mixed within the ferrofluid 15 and is captured in theformed droplets 40. An externally applied magnetic field can be used tofirst generate the droplets 40 containing the drug or medicament. Asecond or different externally applied magnetic field can then beapplied to pull the generated droplets 40 through the porous membrane 50where they enter the second phase 52. The second phase 52 may includebodily or interstitial fluids into which the droplets 40 dissolve ormerge; thereby releasing the drug or medicament contained in thedroplets 40. This particular embodiment is advantageous because itpermits dosing over a large dynamic range as one can control the amountof very finely quantized volumes of droplets 40 (e.g., picoliters tonanoliters per droplet) that are pulled or forced through the porousmembrane 50. Further, this can be accomplished as needed throughfeedback with a sensing system integral with the device 10 or on demandby the user or other health care professional. In addition, thisembodiment of the microfluidic device 10 permits localized delivery ofdrugs. Enough drug or medicament mixed with a ferrofluid may bepre-loaded into the implanted microfluidic device 10 such that drug canbe delivered over an extended period of time (e.g., weeks or months)without exhausting the supply of drug. Furthermore, the embodiment ofFIG. 6A could be used in a wearable format for transdermal drugdelivery. Pores could be created in the skin using microneedles,iontophoresis, or other mechanisms, then controllable drug release couldbe performed when the released droplets 40 containing drugs from theporous membrane 50 are in contact with the pores created in the skin. Inthis case, there is no need for injection using large needles.

The embodiment of FIG. 6C could be used for controlled delivery ofreagents or drugs containing magnetic nanoparticles 17 by implanting thedevice 10 preferably near the skin where a magnetic field could beeasily applied externally. In addition, by incorporating a smallpermanent magnet on top of the membrane 50 for releasing droplets 40,the device 10 could be implanted anywhere in the body and the drug couldbe released intermittently using a programmed schedule or beingactivated remotely using a wireless controller.

One possible drug could be ferumoxytol that is used for treatment ofiron deficiency. Ferumoxytol containing droplets 40 can be generatedwith or without a surfactant. If surfactant is not used, after thedesired numbers of droplets 40 are formed, the droplets 40 can coalesceafter a few minutes and then these droplets 40 are transferred to thesecond phase (e.g., the bodily fluid bathing or surrounding the device10) by applying magnetic force such that the coalesced-droplets 40 couldpass through the porous membrane 50 easier. To avoid undesired releaseof the drug by other external magnetic fields the distance between theferrofluid reservoir 12 and the porous membrane 50 could be adjusted sothat while droplets 40 are squeezing through the porous membrane 50 nomore droplets 40 are generated at the terrace region 22. Differentsections of the device 10 could also be coated with different materials.For example, the inlet region of the device 10 could be coated withanother layer of polymer, etc. so that it acts as a diffusion barrierand the drug will not diffuse into the body over time. These coatingscould be applied to other regions of the device 10.

In still another embodiment, the microfluidic device 10 may includegeometrically designed microfluidic channels 14 and possibleintermediate chambers or reservoirs to thereby make the process ofdroplet release dependent on the spatial and temporal location of theexternal magnets 30, 36 for more controllability. That is, a predefinedsequence of magnetic field directions and strengths would be needed torelease drug-containing droplets 40 that would not be likely to exist innormal daily events. For implanting the microfluidic device 10, theferrofluid reservoir 12 may be sealed which could be done by clamping orbonding another PDMS layer (or other polymers and materials) from thetop once the drug is loaded in the microfluidic device 10.

FIG. 6B illustrates an alternative embodiment of the microfluidic device10 that incorporates the porous membrane 50. In this embodiment, thereis another layer or substrate 54 that is situated atop the microfluidicdevice 10 and defines a chamber 56 for collecting the droplets 40 thatare generated in the microfluidic device 10. In one aspect, this chamber56 may be removed from the microfluidic device 10 so that the droplets40 can be transported for further processing or analysis. Alternatively,the chamber 56 may be connected to one or more additional microfluidicchannels (not shown) that are integrated as part of the microfluidicdevice 10 so that the droplets 40 can be delivered for downstreamreaction or analysis which is useful for point-of-care applications. Thedroplets 40 are created in the same manner as described above and amagnet 36 is used to pull the droplets 40 into the chamber 56.

In the embodiments of FIGS. 6A and 6B, since droplet generation is verycontrollable using this system, one can emulsify a certain volume of asample into droplets 40 and then release it to another phase by forcingor squeezing it through the porous membrane 50 by applying magneticforce over time. This can all be done without traditional displacementor vacuum pumps which are difficult to miniaturize for applications forexample in precise continuous and dosed drug delivery.

FIG. 6D illustrates one embodiment of an implantable device 10 that canbe implanted inside the body of a subject (e.g., mammal). The device 10is similar to that described above with respect to FIGS. 6A and 6C inthat a porous membrane 50 is provided that is permeable to droplets 40that contain a drug or medicament and a ferrofluid which can then leavethe device 10 and be delivered to the patient. In this embodiment, anelectromagnet 34 is located adjacent the device 10 and is connected todriver circuitry 31 that is powered via an internal power source 33 suchas a battery. A permanent magnet 35 is located above or adjacent (on anopposing side of the device 10 as the electromagnet 34) to the porousmembrane 50 to provide a pulling force that pulls the droplets 40 fromthe continuous phase reservoir 16 through the porous membrane 50 wherethe droplet 40 are exposed to the bodily fluids or tissue of the subjectso that the drug is released into the subject.

In one embodiment, the driver circuitry 31 may be preprogrammed togenerate droplets 40 containing a drug a pre-defined times or intervals.In another embodiment, a wireless controller 37 that is located externalto the subject can be used to control the generation of droplets 40 byactuating the electromagnet 34. Actuation may either be manual orautomatic. In this regard, drug containing droplets 40 may be releasedinto the subject at specified intervals or times as well as deliveringthe desired dosage amount by adjusting the length of time thatelectromagnet 34 is in the ON state. Leaving the electromagnet in the ONstate for a longer period of time will generate more droplets 40. Whenthe electromagnet 34 is turned to the OFF state, the magnetic force fromthe permanent magnet 37 pulls the generated droplets 40 through thepermeable membrane 50 where they exit the device 10 and are deliveredlocally to the subject.

FIG. 6E illustrates how the device 10 of FIG. 6D may be used to generatea consistent dosage of drug using droplets 40 by periodically generatingdroplets 40 at different time intervals by energizing the electromagnet34 for a fixed period of time. In this example, a “low” dose of drug isdelivered by energizing the electromagnet 34 for a period of around 10seconds. After the 10 second period has elapsed, the electromagnet 34 isturned to the OFF state and the droplets 40 are then pulled out of thedevice 10 using the permanent magnet 35. FIG. 6E also illustrates a datapoint at the two hour time period where the electromagnetic 34 wasenergized for over 100 seconds which produces a “high” dosage of thedrug due to more droplets 40 being formed. After the electromagnetic 34is turned to the OFF state, the droplets 40 exit the device 10 by beingpulled through the porous membrane 50 via the permanent magnet 35.

FIG. 7 illustrates an operation for making the microfluidic devices 10according to one embodiment. FIG. 7 illustrates a method of making themicrofluidic device 10 of FIGS. 6A and 6B, although it should beunderstood that a similar manufacturing method may be used to make otherembodiments that do not incorporate the porous membrane 50. As seen inoperation 100, a mold 60 is provided that defines the contours of theferrofluid reservoir 12, microfluidic channel(s) 14, and continuousphase reservoir 15. The mold 60 may be made from a material such assilicon and photoresist and may be formed using conventional lithographytechniques. In addition, for this embodiment, two permanent magnets 62are placed on the mold as indicated and sandwich a sheet or disc ofmaterial that forms the porous membrane 50 interposed between bothmagnets 62. The porous membrane 50 may be hydrophilic or hydrophobicdepending on the particular need. The pore dimensions of the porousmembrane 50 may vary from about 0.1 microns to a few 100 microns. Asexplained herein, a PTFE or Nylon membrane 50 having a pore size of 5microns may be used. The porous membrane 50 is pinched between tworelatively strong permanent magnets 62 (e.g., B6301 available from K&JMagnetics, Inc.) during the fabrication process. The purpose of themagnets 62 pinching to the porous membrane 50 is to avoid wetting of theporous membrane 50 with the liquid polymer (described below) that isthen poured over the structure.

After the magnets 62 containing the porous membrane 50 are placed in thedesired location over the continuous phase reservoir 16 location, PDMS(or other curable polymer) that is mixed with a curing agent is gentlypoured over the mold 60 and the sandwich structure formed by the magnets62 and the porous membrane 50. The porous membrane 50 is held in ahorizontal position during this process. Next, the mold 60 and PDMSstructure is placed in an oven for about five hours at 65° C. to cure tocreate the PDMS structure or layer 26. The end result of this process isillustrated by operation or step 110 in FIG. 7 . Next, the PDMSstructure 26 is cut away from the mold 60 and the two magnets 62 areremoved from the top and bottom of the porous membrane 50 and the PDMSstructure 26 and an access passageway or hole is formed in the PDMSstructure 26 to enable filling the ferrofluid reservoir 12. The PDMSstructure 26 is then bonded to a substrate 28 (e.g., glass slide forcertain embodiments). The final device is illustrated in operation 120and incorporates the porous membrane 50 in a top region of thecontinuous phase reservoir 16. As an alternative to forming theferrofluid reservoir 12 using the mold 60, the ferrofluid reservoir 12could be formed using a punching tool (not shown) that generates theferrofluid reservoir 12 in the PDMS layer 26. After filing theferrofluid reservoir 12 a smaller patch of PDMS (not shown) may beapplied over the hole or access passageway to seal the ferrofluidreservoir 12.

To use the microfluidic devices 10, portions of the device may need tobe first treated to alter their surface chemistry. For example, surfacesof the continuous-phase reservoir 16 may be treated for a certain timewith an appropriate solution or chemistry to become hydrophobic orfluorinated before introducing the oil in the continuous-phase reservoir(or hydrophilic when the continuous phase is water). For example, foroil-based solutions in the continuous-phase reservoir 16, the surfacesmay be pre-treated with RAIN-X® (for Pico-Surf™ based surfactant/oilsolution) or trichloroIJ1H,1H,2H,2H-perfluorooctyl) silane (SigmaAldrich) (for FC-40, Fluorinert). For an embodiment that uses anoil-based fluid in the continuous-phase reservoir 16, the oil-basedfluid is introduced via the outlet 22 and into the continuous-phasereservoir 16. The oil-based fluid may include a mixture of a surfactantthat is contained in a fluorocarbon carrier oil. For example, Pico-Surf1™ which includes 2% or 3% surfactant in Novec™ 7500 may be used(available from Dolomite Microfluidics, catalog numbers 3200211 and3200214). Yet another example of an oil-based fluid includes FC-40 orFluorinert™ (available from Sigma-Aldrich, catalog number F9755). Ofcourse, these specific types of fluids are exemplary and other oil-basedfluids may be used. In some embodiments, to avoid trapping of bubblesinside the continuous phase reservoir 16, the ferrofluid reservoir 12can be covered for dead-end filling (either by another layer of PDMSbonded or clamped from the top or simply by pressing that region). Theferrofluid 15 is then loaded into the one or more ferrofluid reservoirs12 after loading with the microfluidic device 10 with the oil phase. Asexplained herein, the ferrofluid 15 may include a reagent or sampletherein that is intended to be encapsulated or entrained in the dropletsor emulsions 40. In some embodiments, the ferrofluid reservoir 12 mayalso be covered with another layer of PDMS or a substrate 54 like thatillustrated in FIG. 6B in order to completely enclose the microfluidicdevice 10. Droplets 40 will still form and negative pressure created atthe ferrofluid reservoir 12 does not prevent droplet formation. In thisformat, by applying a magnetic field (as explained below) a certainnumber of droplets 40 are formed and backflow of the continuous phasestops droplet generation. To continue droplet 40 generation, the magnet30 is moved away from the step region 20 temporarily and then relocatedat the step again. This approach may be used to control the number ofdroplets 40 that are released so as to avoid undesired release ofreagents which may be particularly suited for the microfluidic device 10embodiment of FIG. 6C.

The moveable external magnet 30 is then moved using the stage or track32 to the desired distance (D) away from the step 20 to initiate dropletgeneration. For example, the external magnet 30 is brought adjacent tothe bottom of the microfluidic device 10 (if not already positionedthere) and the distance of the external magnet 30 from the step or wall20 is adjusted from 0 to about 2,500 μm downstream (x direction) of thestep or wall 20. Alternatively, if one or more electromagnets 34 areused, the various electromagnets 34 or sections are energized to mimic amagnetic field to drive the ferrofluid 15. As the fluid reaches the stepregion 18, it starts to pinch off due to surface tension effects anddroplets 40 are formed.

Various parameters may be adjusted to control the size of the droplets40 as well as their formation rate. As noted herein, as the fluid passesthe step 20, pinch off occurs passively to create the droplets 40 of ageometrically-determined size. The length of the terraced region 24 maybe varied to adjust the size of the droplets 40. For example, largersized droplets (e.g., 125 μm diameter) were found to be generated with aterrace region 24 having a length of 90 μm as compared to droplets(e.g., 85 μm diameter) for a terraced region 24 having a length of 60μm. Even without the terraced region 24 droplets will, however, stillform.

Likewise, as explained herein, the rate of droplet generation may beincreased by reducing the distance (D) between the moveable externalmagnet 30 and the step 20. Conversely, the droplet generation rate maybe decreased by increasing the distance (D) between the moveableexternal magnet 30. In addition, it has been found that by increasingthe surfactant concentration the droplet generation rate increases.Droplet generation thus increases as a function of increasing magneticforce and decreasing surface tension. By adjusting the position of theexternal magnet 30 to create a higher magnetic field gradient, dropletgeneration increases linearly with magnetic field gradient for both thePico-Surf™/Novec™ 7500 continuous phase as well as the FC-40 continuousphase as seen by FIGS. 5A and 5B. In addition, increasing the surfactant(from 0% to 5% Pico-Surf™ in Novec™ 7500) reduces the surface tensionforce and droplet generation increases as seen in FIG. 5C. Note that insome embodiments, surfactant may not be needed or desired. For example,if the generated droplets 40 will be delivered to a subject as atherapeutic or medicament, one may not want the presence of thesurfactant. Still other embodiments may require the presence of thesurfactant to prevent coalescence of the droplets 40 post-formation. Forexample, for assays that are performed in individual droplets 40 andthen imaged; the separation of droplets 40 is required. In suchinstances, surfactant may be present to prevent droplet coalescence.

The driving force also increased with the addition of more magneticnanoparticles 17 to the solution (e.g., increasing the volume fractionof magnetic nanoparticles 17) which resulted in a higher dropletgeneration rate as seen in FIG. 8A. The droplet generation rateincreases by increasing the concentration of the magnetic nanoparticles17. Even diluted ferrofluid 15 down to less than 10% of the initialstock solution can create droplets 40. The ability to create droplets 40at lower ferrofluid 15 concentrations is important to be able to use thesystem for downstream assays. In this case, a sample volume, polymerprecursor, or reagent volume can be mixed with the ferrofluid 15 in theferrofluid reservoir 12 and still maintain the ability to createdroplets 40 with more dilute mixed ferrofluid solution. When thecontinuous phase is Pico-Surf™, the droplet generation rate can beadjusted to be in a range between 0 to 12 droplets per second permicrofluidic channel by changing the concentration of the magneticnanoparticles 17 when the permanent magnet distance is fixed at adistance of 150 μm from the step 20. When FC-40 was used as thecontinuous phase the droplet generation rate is much lower compared toPico-Surf™. Note that a parallelized version of the microfluidic device10 such as that illustrated in FIG. 1C has much higher dropletgeneration rates due to parallel droplet formation (e.g., 100 dropletsper second or higher).

The viscosity of the oil phase also plays a role in the rate of dropletformation. Decreasing the viscosity of the oil phase reduces fluidicresistance and droplet generation increases. With reference to FIG. 8B,by decreasing the viscosity (1.24 cP (Novec™ 7500) instead of 3.5 cP(FC-40)) fluidic resistance decreases and droplet generation increases(surface tension of Novec™ 7500 and FC-40 are 16.2 and 16 mN m⁻¹respectively). The maximum droplet generation rate that wasexperimentally achieved with the cylindrical magnet (K&J Magnetics-D68)is about 80 droplets per second per connecting channel for 5 percentPico-Surf™ oil using EMG 408 ferrofluid 15. Consequently, a 10 μlsolution would be emulsified to 85 μm droplets in less than 10 (ten)minutes.

As explained herein, the a microfluidic device 10 such as thatillustrated in FIG. 1D which has multiple ferrofluid reservoirs 12 a, 12b, 12 c may be used to mix reagents on-chip. One of the importantfeatures required for droplet or digital microfluidics is the ability tomix reagents on-chip and formal compartmentalized droplets afterwards.This is critical for some analytical approaches that rely on reactionsbecause if the reactive reagents are mixed in a one-inlet device,reactions can initiate as soon as mixing occurs. Therefore, all dropletswill contain products of the reaction such that concentration-dependentdetection of the target present in each droplet is not possible, orreaction conditions are not controllable. FIG. 1D illustrates oneembodiment that uses three ferrofluid reservoirs 12 a, 12 b, 12 calthough two or more such reservoirs 12 may be used. For example, in atwo ferrofluid reservoir 12 embodiment, the moveable external magnet 30may be positioned downstream of the step 10 (e.g., at a distance (D) of50 μm) to have an equal magnetic body force on both solutions attractingthem toward the droplet generating step 20 for uniform mixing. In thethree ferrofluid reservoir embodiment of FIG. 1D, the three separatereagent are combined immediately upstream of step 20 where droplets 40are generated. This enables reaction components to be quickly entrainedin droplets 40. Note that while FIG. 1D illustrates the fluids containedin the respective ferrofluid reservoirs 12 a, 12 b, 12 c being combinedat a common junction it is possible two fluids are combined upstreamprior to be being joined by the third or last ferrofluid 15 solution.Thus, mixing in a desired sequence of operations can be performed. Inaddition, various concentrations or different types of magneticnanoparticles 17 can be used to adjust the relative amounts of thecomponents that end up entrained in the droplets 40.

In another embodiment, a middle ferrofluid reservoir 12 b contains noreagent, while two side reservoirs 12 a, 12 c contain reactivesample/reagent and no interaction is observed between the fluid presentin the two side reservoirs while flowing through the connecting channelto the emulsification junction. Mixing is only initiated once a droplet40 is formed. In a related embodiment, the different channels 14extending from the different reservoirs 12 a, 12 b, 12 c possessdifferent fluidic resistance to control the relative flow rate of thefluids in each of the reservoirs that flow into the emulsificationjunction. One could also vary the amount of ferrofluid 15 with separatereagents in different ferrofluid reservoirs 12 and mix these reagentswith controlled flow rates that depend on the ferrofluid 15 amountbefore droplet generation.

A wide variety of species, reagents, and cells can be used as part ofthe sample. Samples that could be introduced include diagnostic orresearch samples that include drugs, mammalian cells, bacteria, viruses,nucleic acids, protein biomarkers, microRNA, and/or exosomes. Samples orintroduced fluids could also consist of polymer precursors. Thereactions occurring in the droplets 40 could include nucleic acidamplification (e.g., polymerase chain reaction (PCR), loop-mediatedisothermal amplification (LAMP), multiple displacement amplification(MDA), homogeneous entropy-driven biomolecular assay (HEBA), or otheramplification strategies) followed by analysis of fluorescence usingfluorophore-quencher probes or intercalating dyes. A digital nucleicacid amplification and readout could be conducted for example. Thisreadout may be conducted following droplet generation in a reservoir orat some other downstream located chamber or region of the device 10 withor without having been pulled through the porous membrane 50.Alternatively, digital immunoassays could be performed in the droplets40. In fact, any assay conducted in confined volumes using other methodsof forming droplets 40, could be performed in this system.Alternatively, an amplified immunoassay could be performed in thedroplets 40 using a fluorescent or colorimetric readout targeting amolecule in solution (e.g., cytokine from an activated or restingleukocyte or antibody produced by a B cell or hybridoma) or attached toa bioparticle in the sample (e.g., cell, virus, bacterium).

Alternatively, analysis of secretions from cells could be performedusing an immunoassay or fluorogenic substrates for enzymes (e.g.,substrates for proteases, caspases, or esterases), using the confinedvolume of the droplet 40 to concentrate secretions for readout. Toenhance detection, magnetic droplets 40 could be brought to a desiredsurface or location using magnetic control, or magnetic nanoparticles 17in the droplets 40 could be pulled to the side or bottom of a droplet 40to prevent interference with biochemical assays or imaging. The droplets40 may also be pulled through a porous membrane 50 as described hereinand exposed to a suspension of cells contained on the top or opposingside of the porous membrane 50. Magnetic droplets 40 could also bebrought to a reservoir surface using a magnetic field to initiate areaction with a surface-bound reagent. Another reaction would includesingle-cell whole genome amplification within each droplet 40 with orwithout barcoded magnetic nanoparticles 17 (e.g., according to theDropseq protocol). Another approach is to perform whole genomeamplification across many droplets from a sample to reduce bias inamplification (e.g., see Yanyi Huang PNAS 2015).

Readout of the assays could be done with a variety of techniques, e.g.,using a lens-based microscopic system that images a downstream dropletreservoir or the like to perform quantification. Alternatively,lens-free imaging systems described by Ozcan et al. (e.g., DigitalReadout Platform for Water-In-Oil Droplet Immunoassays Running on aCell-Phone for Point of Care Viral Load Sensing, MicroTAS 2012; The 16thInternational Conference on Miniaturized Systems for Chemistry and LifeSciences, Okinawa, Japan (Oct. 28-Nov. 1, 2012), using over-the-counterreaders/imagers such as mobile phones, digital cameras, or flatbedscanners. In the embodiment where droplets 40 are guided to an outletchannel in single file a flow cytometry type reader setup consisting ofa filtered excitation and emission collected by a PMT or photodiode ispossible.

In some embodiments that utilize a porous membrane 50, there is no needfor a magnet 36 that is used to pull the droplets 40 through a porousmembrane 50. For example, if the porous membrane 50 has pore sizes thatare large (e.g., larger than diameter of the droplet 40) and thedroplets 40 experience a buoyant force within the continuous phase, thedroplets 40 may naturally rise and pass through the porous membrane 50.This process can be aided by choosing a high density continuous phase(e.g., like Pico-Surf™). If there are particles or other speciescontained within the droplets 40, this method could be used to separatedroplets 40 based on different densities and sizes (e.g., differentnumbers of encapsulated particles or species).

The porous membrane based embodiment of FIGS. 6A and 6B could also beused as a microfluidic magnetometer for fluids. If the release rate ofdroplets 40 through the porous membrane 50 is calibrated having a magnet36 with a known magnetic strength and a fluid with a known magneticsusceptibility, then one can use the observed release rate of droplets40 in a fluid with unknown magnetic properties to calculate or determineits magnetic susceptibility.

In still another application of the porous membrane based embodiment ofFIGS. 6A and 6B, plasma may be purified from blood for low volumeprocessing. After blood is mixed with magnetic nanoparticles 17,droplets 40 are generated by applying a magnetic field and then thedroplets 40 are attracted toward the porous membrane 50 by moving themagnet 30, 36 and components smaller than the pore size of the porousmembrane 50 will squeeze or pass through the porous membrane 50 andlarger components remain in the microfluidic device 10.

Still another application of the porous membrane based embodiment ofFIGS. 6A and 6B is in applications or experiments where access to oxygenis needed. For example, cells may be encapsulated in droplets 40 andbrought adjacent to the porous membrane 50 that is exposed on one sideto air to provide access to oxygen. Oxygen may be exchanged with thecells through the small volume of liquid contained in the droplets 40.

This technique should impact the variety of applications in whichmicrofluidic confinement or droplet generation is used for assays(especially digital assays) or fabrication. One main application wouldbe using this device for digital assays at a point-of-care, where onecould easily manipulate samples (mix, emulsify and move) and reagents inthe form of discrete droplets (Digital PCR, etc.). In this case, nobulky pumps or complex footprint would be needed for the instrument.This could bring digital assays to point-of-care diagnostics instead ofanalog PCR or other nucleic acid tests for example for pathogen nucleicacid analysis. Digital assays have some advantages in terms ofquantification compared to analog assays. In addition analysis ispossible from a small volume given the small dead volume of our systemcompared to pump-based systems. The complexity of multiple assaysteps/reagents is also reduced when pulling magnetic fluid from separatereservoirs instead of pushing fluids together using pumping.

Another application is that the microfluidic device 10 can be used as acontrolled mechanism for time-sensitive reactions, where reagents shouldonly be mixed at a certain time by having two or more separatereservoirs containing different reagents mixed with ferrofluid havingdifferent concentrations of magnetic nanoparticles 17. Thus, differentreservoirs may be loaded with ferrofluids 15 with varying concentrationsof magnetic nanoparticles 17. Ferrofluid reservoirs 12 may also belocated at different locations on the microfluidic device 10 such thatthey experience differential forces from the magnet 30. These optionscould be used to mix different amount of each reagent in the droplet 40.

As explained herein, it is also possible that two reagents merge andthen downstream the third reagent mixes with those two. This gives extratime for the first two reagents to start a specific reaction and thenthe third one could be added at the desired time before the stepemulsification region. This can be controlled by designing the order orsequence of junctions of the various microfluidic channels 14 prior tothe step region 18. In this case one or more permanent magnets could beused. The fluorescent readout could be one way of analyzing this type ofexperiment. One can also adjust the flow rate of each reagent by addingdifferent concentration of magnetic nanoparticles 17 to the differentferrofluid reservoirs 12.

Another application could be making different types of magnetic polymeror hydrogel particles (even for example Janus particles) if UV isapplied right after droplet generation to polymerize the droplets 40, ora reaction requiring two components is initiated upon mixing twostreams. In such an embodiment, the ferrofluid would likely be anorganic-based fluid while the continuous phase would be aqueous-based.

Another application of the device and method is active sorting of cellsand particles encapsulated in droplets 40 containing ferrofluid 15. Forexample, when the droplet 40 is forming at the step region 18, theencapsulated particle is detected (either by the size measurement orfluorescence signal of the labeled particles) then the magnet 30 (or adifferent magnet) could move to the top part of the continuous phasereservoir 16 to collect those droplets 40 there; and when the droplet 40is empty or smaller particles are detected the magnet 30 moves to thebottom of the reservoir to collect these type of droplets in a separatelocation.

In addition, if the continuous-phase reservoir 16 is long enough one canmeasure the velocity of the formed droplets 40 and depending on thecontent of the droplet 40 (e.g., the amount of magnetic nanoparticles17, particles or cells inside droplet, etc.) the droplets 40 will movewith different velocities toward the magnet 30. This could also be usedas a metric for analyzing how pure a sample is or collecting only afraction of droplets 40 with particular reagents.

While embodiments of the present invention have been shown anddescribed, various modifications may be made without departing from thescope of the present invention. For example, features or aspects of oneembodiment may be incorporated in other embodiments even if notspecifically identified as being substitutable. The invention,therefore, should not be limited, except to the following claims, andtheir equivalents.

What is claimed is:
 1. An implantable microfluidic device for deliveringa drug to a subject comprising: a ferrofluid reservoir disposed in themicrofluidic device and containing a ferrofluid and/or drug therein; acontinuous-phase reservoir disposed in the microfluidic device andcontaining an oil phase therein, the continuous-phase reservoircontaining a permeable membrane therein through which the ferrofluidand/or drug passes; one or more microfluidic channels connecting betweenthe ferrofluid reservoir and the continuous-phase reservoir, thecontinuous-phase reservoir comprising a step region having an increasedheight as compared to a height of the one or more microfluidic channels;a permanent magnet disposed adjacent to the permeable membrane on afirst side of the device; and an electromagnet disposed on a second sideof the device and connected to driver circuitry configured to power theelectromagnet.
 2. The implantable microfluidic device of claim 1,further comprising a wireless controller, wherein the wirelesscontroller controls operation of the electromagnet.
 3. The implantablemicrofluidic device of claim 2, wherein the wireless controller actuatesthe electromagnet for one or more preset time intervals.
 4. Theimplantable microfluidic device of claim 1, wherein the electromagnet isconnected to driver circuitry and an internal power source.
 5. Theimplantable microfluidic device of claim 1, wherein the ferrofluidcomprises the drug.
 6. The implantable microfluidic device of claim 1,wherein the drug is conjugated to magnetic nanoparticles in theferrofluid.
 7. The implantable microfluidic device of claim 1, whereinthe ferrofluid is mixed with the drug.
 8. A microfluidic device fordelivering a drug to a subject comprising: a ferrofluid reservoirdisposed in the microfluidic device and containing a ferrofluid and/ordrug therein; a continuous-phase reservoir disposed in the microfluidicdevice and containing an oil phase therein, the continuous-phasereservoir containing a permeable membrane therein through which theferrofluid and/or drug passes; one or more microfluidic channelsconnecting between the ferrofluid reservoir and the continuous-phasereservoir; and a first permanent magnet or electromagnet disposedadjacent to a first side of the microfluidic device and configured toform droplets of ferrofluid and/or drug within the continuous-phasereservoir.
 9. The microfluidic device of claim 8, further comprising asecond permanent magnet or electromagnet disposed adjacent to a second,opposing side of the microfluidic device and configured to pull thedroplets of ferrofluid and/or drug across the permeable membrane. 10.The microfluidic device of claim 8, wherein the permable membrane of themicrofluidic device is positioned adjacent to the skin of a subject. 11.The microfluidic device of claim 8, wherein the ferrofluid comprises thedrug.
 12. The microfluidic device of claim 8, wherein the drug isconjugated to magnetic nanoparticles in the ferrofluid.
 13. Themicrofluidic device of claim 8, wherein the ferrofluid is mixed with thedrug.
 14. The microfluidic device of claim 8, wherein thecontinuous-phase reservoir comprises a step region having an increasedheight as compared to a height of the one or more microfluidic channels.15. A method of delivering a ferrofluid and/or drug to a subjectcomprising: positioning a microfluidic device on or within a subject,the microfluidic device comprising: a ferrofluid reservoir disposed inthe microfluidic device and containing a ferrofluid and/or drug therein;a continuous-phase reservoir disposed in the microfluidic device andcontaining an oil phase therein, the continuous-phase reservoircontaining a permeable membrane therein through which the ferrofluidand/or drug passes; and one or more microfluidic channels connectingbetween the ferrofluid reservoir and the continuous-phase reservoir; andapplying a first magnetic field to the microfluidic device to generatedroplets comprising the ferrofluid and/or drug; and applying a secondmagnetic field to the microfluidic device to transport the generateddroplets across the permeable membrane and in contact with the subject.16. The method of claim 15, wherein the first and/or second magneticfields are applied with a permanent magnet.
 17. The method of claim 15,wherein the first and/or second magnetic fields are applied with apermanent magnet.